EP3689290B1 - Verfahren zur herstellung einer teil- oder totalprothese sowie prothese erhältlich nach diesem verfahren - Google Patents

Verfahren zur herstellung einer teil- oder totalprothese sowie prothese erhältlich nach diesem verfahren Download PDF

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Publication number
EP3689290B1
EP3689290B1 EP20163304.7A EP20163304A EP3689290B1 EP 3689290 B1 EP3689290 B1 EP 3689290B1 EP 20163304 A EP20163304 A EP 20163304A EP 3689290 B1 EP3689290 B1 EP 3689290B1
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EP
European Patent Office
Prior art keywords
prosthetic
dental
tooth
teeth
dental arch
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EP20163304.7A
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German (de)
English (en)
French (fr)
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EP3689290A3 (de
EP3689290A2 (de
EP3689290C0 (de
Inventor
Klaus Dr. Ruppert
Christian Bauer
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Kulzer GmbH
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Kulzer GmbH
Kulzer and Co GmbH
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Publication of EP3689290B1 publication Critical patent/EP3689290B1/de
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C13/00—Dental prostheses; Making same
    • A61C13/0003—Making bridge-work, inlays, implants or the like
    • A61C13/0004—Computer-assisted sizing or machining of dental prostheses
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C13/00—Dental prostheses; Making same
    • A61C13/0001—In-situ dentures; Trial or temporary dentures
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C13/00—Dental prostheses; Making same
    • A61C13/0003—Making bridge-work, inlays, implants or the like
    • A61C13/0006—Production methods
    • A61C13/0013—Production methods using stereolithographic techniques
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C13/00—Dental prostheses; Making same
    • A61C13/0003—Making bridge-work, inlays, implants or the like
    • A61C13/0006—Production methods
    • A61C13/0019—Production methods using three dimensional printing
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C13/00—Dental prostheses; Making same
    • A61C13/01—Palates or other bases or supports for the artificial teeth; Making same
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C13/00—Dental prostheses; Making same
    • A61C13/08—Artificial teeth; Making same
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C13/00—Dental prostheses; Making same
    • A61C13/08—Artificial teeth; Making same
    • A61C13/081—Making teeth by casting or moulding
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C13/00—Dental prostheses; Making same
    • A61C13/08—Artificial teeth; Making same
    • A61C13/082—Cosmetic aspects, e.g. inlays; Determination of the colour
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C13/00—Dental prostheses; Making same
    • A61C13/08—Artificial teeth; Making same
    • A61C13/09—Composite teeth, e.g. front and back section; Multilayer teeth
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C13/00—Dental prostheses; Making same
    • A61C13/10—Fastening of artificial teeth to denture palates or the like
    • A61C13/1003—Fastening of artificial teeth to denture palates or the like by embedding in base material
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C13/00—Dental prostheses; Making same
    • A61C13/34—Making or working of models, e.g. preliminary castings, trial dentures; Dowel pins [4]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C19/00—Dental auxiliary appliances
    • A61C19/003—Apparatus for curing resins by radiation
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
    • A61C5/00—Filling or capping teeth
    • A61C5/70—Tooth crowns; Making thereof
    • A61C5/77—Methods or devices for making crowns

Definitions

  • the invention relates to a method for producing a dental prosthetic molded part, such as a complete denture, which is produced in multiple layers from a generatively produced full-body model, at least one prosthetic tooth or a prosthetic tooth arch, the prosthetic teeth having a lumen on the inside of the tooth neck, into which a dentine-colored, polymerizable composition is filled becomes.
  • This composition is then polymerized in at least one step.
  • the at least one prosthetic tooth with a dentin-colored composition is arranged with its cervical side on the tooth-side surface of the prosthetic base and pressed together.
  • the resulting complete denture is then completely cured in a light curing device.
  • the invention also relates to the prosthetic molded parts obtainable by the process according to the invention.
  • acrylate-based dentures using the RP process is still subject to severe restrictions.
  • Multicolored dentures or dentures made from different polymer materials (e.g. for enamel and dentin materials) for the production of high-quality and aesthetic dentures have so far only been possible to produce using complex RP machines with multiple material chambers or using complex gluing and joining techniques.
  • the DE102011102095A1 discloses the production of multi-part prostheses, whereby the at least two, in particular 3 + n, individual components, which can be connected to one another via at least one contact surface, are produced using generative processes.
  • the disadvantage of these additively manufactured, adjacent individual components is that these individual components must be manufactured with an extremely precise fit in order to avoid internal surfaces in the prostheses. Such internal surfaces, which cannot be equated with internal interfaces, can occur after shrinkage or due to distortion after additive manufacturing. These internal surfaces or cracks affect the aesthetics of translucent materials, as well as the stability and hygiene of the prostheses.
  • DE102007010624A1 discloses a method for the stereolithographic production of a molded part from at least two different solidifiable masses by solidifying layers of the solidifiable masses on the underside of a support that can be immersed in the masses. To carry out the time-consuming process, a complex device with a specific container arrangement is used.
  • US2014/308624A1 discloses the 3D manufacturing of a denture base and teeth both in one unit or a denture base and individual teeth.
  • US2014/167300 discloses light-curing compositions for making a denture base and artificial teeth that are assembled after printing.
  • the task was to provide an economical process that allows the production of high-quality and very aesthetic dentures using a generative process such as rapid prototyping. Furthermore, there was the task of simplifying the procedure and shortening the duration of the procedure. In addition, the task was to provide a high-quality, aesthetic denture that has an aesthetic similar to tooth enamel as well as translucency, as well as a dentin-colored core that replicates a natural tooth. Preferably An economical process should enable the production of multi-layered or multi-colored prosthetic teeth.
  • the tasks are solved by first constructing the complete denture digitally, as exemplified in Figure 1 shown.
  • the prosthesis is then converted into a part for the prosthesis base plate using file splitting (dividing the digital data), see for example Figure 2a , and a part for the prosthetic teeth, see Figure 2b , disassembled.
  • the data set of the prosthetic teeth with an indicated cutting edge is initially an open shell (consisting only of surfaces 1) and can be referred to as an open surface shell.
  • This surface with an opening synonymous lumen in the direction of the prosthesis base plate is, for example, in Figure 1 shown.
  • the pure surface shell - synonymous with digital data of the surface model - consists of a connection of points that describe the geometry.
  • the points of a point cloud are digitally connected so that they form triangles.
  • the size of the triangles adapts to the geometry, so there is no one-size-fits-all triangle. Since it was created digitally, the wall thickness of the surface shell is zero, i.e. the surface shell has a wall thickness of 0 mm.
  • This wall thickness is determined during the construction of the complete denture and reflects the aesthetic shape of the teeth.
  • Preferred wall thicknesses are in the range from 0.005 mm to the center of the tooth, for example from 0.005 mm - 5 mm.
  • a prosthetic tooth is obtained without an internal lumen (synonym: cavity) for filling with a dentin-colored, dental composition.
  • This full-body model is then broken down into parallel layers using software, as required in the subsequent printing process.
  • the full body model is cut in the software into parallel layers with a respective layer thickness of approximately 5 to 200 ⁇ m.
  • the prosthetic teeth can preferably be made from at least one or different light-curing materials similar in color to tooth enamel using rapid prototyping processes (RP processes).
  • RP processes rapid prototyping processes
  • the individual teeth are advantageously connected to form a dental arch and printed at the same time.
  • the teeth can essentially be printed individually, preferably being connected to one another at least cervically.
  • the prosthesis base (plate) can be produced using a generative process, such as the RP process.
  • the denture base is made from a gingiva-colored, polymerizable dental composition.
  • the cavity synonymous with the lumen of the tooth created or the depressions of the dental arch created is completely filled with one or more flowable, dentin-colored, light-curing, dental compositions. Curing can take place either layer by layer or in one step for all layers - with the exception of the last layer - at the same time.
  • the cavity filled with unhardened and optionally hardened composition synonymously the lumen of the prosthetic tooth or the prosthetic teeth of the dental arch, is pressed together with the prosthetic base plate; any excess or overflowing, light-curing composition can be removed.
  • the compressed denture base and the dental arch can then be placed in be cured using a light curing device.
  • the denture base must either have a dispersion layer or the surface must have been previously activated with Palabond, for example. During this hardening, all components are permanently bonded together without any edge gaps and at the same time the final strength of the prosthetic material is created.
  • This post-curing or bonding is carried out with intensive light in a wavelength tailored to the respective photoinitiators, e.g. at 385 nm (Lucirin TPO) or at approx. 100 - 600 nm camphorquinone).
  • a suitable lighting device is, for example, the HiLite power laboratory light lamp from Heraeus Kulzer GmbH.
  • stereolithography or DLP processes processes for curing liquid monomers using UV or visible light
  • RP processes processes for curing liquid monomers using UV or visible light
  • Other conceivable generative or structural manufacturing processes for producing dentures and denture base plates include laser sintering or 3D printing, such as fused deposition modeling.
  • the virtual model of the surfaces of the teeth and the denture base can be generated according to known methods from the prior art using a computer program and provided as digital data.
  • the (A) (i) digital data of a virtual model of the surfaces (STL file) of the molded part can be captured and/or created in a known manner. For example, by scanning a partially edentulous or edentulous jaw, an impression or a model with or without teeth.
  • the digital teeth can be used from a digital library to generate the digital data of a virtual model of the surfaces (STL file) of the molded part or the digital data of the model of the prosthetic teeth, for example to adjust the cervical area of the prosthetic teeth.
  • the digital data of the virtual model of the surface is split (file splitting).
  • the digital data of the models of the prosthetic teeth and the prosthetic base plate are available in isolation and are individually adjusted in the cervical and tooth-side areas.
  • the layers according to the invention correspond to slices of a defined layer thickness.
  • the layers or slices are obtained by so-called slicing.
  • the layers according to the invention include disks, such as in DLP processes, as well as layers that are obtained by depositing tracks, such as in the FDM process.
  • an open lumen is created for the virtual model of the surface of the at least one prosthetic tooth, the prosthetic teeth or the dental arch on the contact surface with the prosthetic base plate, which can be closed again by reattaching the prosthetic base plate.
  • the virtual model of the prosthesis base is calculated as a full body model 10 and digitally divided into parallel layers.
  • the surface of the denture base plate in the area in which the virtual at least one denture tooth, the denture teeth or the dental arch were cut off after file splitting is an opening in the surface that is closed in the virtual model of the denture base.
  • the virtual model of the prosthesis base is calculated as a full-body model and is then preferably cut into parallel layers that provide the data for the RP process. For the printing process, the digital data is referenced and volume shrinkage is taken into account.
  • the digital data of the virtual model of the surface of the prosthesis base (plate) present in step (v) preferably shows a positive fit in the at least one area in which the virtual model of the at least one prosthetic tooth or teeth, in particular of the dental arch, is inserted Fit and/or cohesive fit to the cervical, lower and/or inner surface of the full body model in the area of the respective tooth neck of the at least one prosthetic tooth or dental arch.
  • the cervical region of at least one prosthetic tooth 1.2 corresponds to a negative of the corresponding tooth-side region 2.2 of the prosthetic base plate, which is designed as a positive.
  • all areas 1.2 and 2.2 are provided individually as negative and positive for all teeth.
  • all cervical areas of the prosthetic teeth 6 (1 to n) are individually adapted to a tooth-side area 2.2 (1 to n) of the outer surface of the prosthetic base plate.
  • all prosthetic teeth are specifically assigned to a toothless area of the prosthetic base plate, thus coding in the key/lock type takes place. Consequently, the connection point between the prosthetic tooth and the base plate is preferably in the form of depressions and correspondingly shaped counterparts as a clear fit.
  • the external dimension of the surfaces does not change.
  • the wall thickness only expands inwards into the interior of the teeth and reduces the lumen or cavity within the surface, possibly down to zero, i.e. a full-body model whose surface in the area of the tooth neck corresponds to a negative of the surface of the denture base.
  • step B the real models of the denture teeth and the denture base are made.
  • the digital model of the prosthesis base can be converted into a full body model in step (v) before carrying out step (vi).
  • the digital model of the prosthesis base can be converted into full-surface layers during or after decomposition into layers after carrying out step (vi).
  • a conversion into printing webs is also conceivable.
  • the production according to the invention is preferably carried out in an RP process in which an entire layer of the polymeric composition is polymerized at the same time.
  • a wall thickness in the virtual full body model of greater than or equal to 0.005 to 3 mm, in particular greater than or equal to 0.025 mm is preferably generated, in particular from 0.025 mm to a full body model without an inner lumen, the cervical, inner surface of the full body model being in the Area of the respective tooth neck corresponds to a negative of the tooth-side outer surface of the prosthesis base.
  • Preferred wall thicknesses are 0.05 to 5 mm, preferably 0.075 to 2.5 mm.
  • the lumen can be provided in a prosthetic tooth, a lumen in each prosthetic tooth or a common lumen across all prosthetic teeth in a dental arch.
  • a lumen is preferably provided for each prosthetic tooth in the front tooth area, while a common lumen can be present in the other teeth of the dental arch.
  • the dental arch of the prosthetic teeth can also have a single lumen. It is clear to the person skilled in the art that every conceivable combination can be produced and is available using the method according to the invention. Therefore, prosthetic teeth or dental arches with the aforementioned wall thicknesses are also the subject of the invention.
  • the virtual full body model obtained in step (iii) in the method according to the invention has a lumen, the dimensions of which depend in particular on the wall thickness.
  • the wall thicknesses of the generatively produced at least one prosthetic tooth, the prosthetic teeth and/or the dental arch produced in the generative process are preferably greater than or equal to 0.025 mm, preferably 0.05 mm to 5 mm, more preferably 0.075 mm to 2 mm or up to a full body without inner lumen, whereby the cervical, inner surface of the solid body in the area of the respective tooth neck corresponds to a negative of the tooth-side outer surface of the prosthesis base.
  • a dental arch points over At least two prosthetic teeth have a common lumen.
  • the prosthetic teeth in the front tooth area each preferably have a lumen.
  • two or more prosthetic teeth can form a virtual full-body model in that they are each connected approximally and form at least part of a dental arch, in particular 2 to 16 teeth, each connected approximally, form a dental arch as a virtual full-body model of an upper or lower jaw. Furthermore, a method is disclosed in which two or more of the generatively produced prosthetic teeth can be connected approximally and form at least part of a dental arch, in particular 2 to 16 teeth are produced, each of which, when connected approximally, form a dental arch of an upper or lower jaw.
  • prosthetic teeth form a virtual full-body model in that they are each connected approximally and form a dental arch, in particular the teeth, each connected approximally, form a dental arch as a virtual full-body model of an upper or lower jaw.
  • the generatively produced prosthetic teeth are connected approximally and form a dental arch, in particular up to 16 teeth are produced, each of which is connected approximally to form a dental arch of an upper or lower jaw.
  • the invention also relates to a dental arch obtainable using the method.
  • the digital layers of the prosthetic teeth, the dental arch and/or the prosthetic base (plate) preferably have a layer thickness (z data) of 5 to 200 ⁇ m, in particular a layer thickness of 25 to 200 ⁇ m, more preferably 25 to 100 ⁇ m, especially preferably from 25 to 50 ⁇ m.
  • the production of the prosthetic molded parts is preferably carried out in a generative process comprising photochemical polymerization (radiation hardening), stereolithography and/or 3D printing.
  • a generative process comprising photochemical polymerization (radiation hardening), stereolithography and/or 3D printing.
  • production takes place in a generative process with homogenized light quantity distribution with a surface light modulator, such as a rapid prototyping method, in which with homogenized light quantity distribution, in particular with an LED projector in which the light quantity distribution is homogenized, as in DE102012224005A1 disclosed.
  • an entire layer of the polymerizable composition, ie the at least one prosthetic tooth, of the prosthetic base can be polymerized with an exposure step or exposure flash.
  • UV/Vis lasers UV/VIS LED projectors
  • UV LED projectors UV LED projectors
  • UV LED projectors can also be used as well as LED projectors with longer wavelength light, e.g. 420 430 nm.
  • the method according to the invention preferably comprises a step of the generative production of the prosthetic tooth, the prosthetic teeth, the dental arch and/or the prosthetic base plate, wherein a photochemical polymerization of a liquid composition comprising monomers and/or polymers occurs triggered by a light source.
  • the light source used is preferably a projector or a laser system, in particular with radiation with a wavelength of 100 to 600 nm, preferably from 180 to 440 nm; an LED projector with radiation around 385 nm or 430 nm is preferably used or a Laser system with radiation with a wavelength between 220 and 440 nm.
  • the partial polymerization can take place after step (B) (viii) and before carrying out step (ix).
  • the at least one lumen is preferably at least partially filled with at least one or more flowable, dentin-colored, UV/VIS-polymerizable dental compositions and polymerized in one or more steps with UV and/or VIS light.
  • the filling can take place in one step or in several steps, for example in 1 to 20 steps, whereby the polymerization of the composition (s) can also take place once or multiple times.
  • steps (A), (B), in particular (viii) and (ix), preferably (ix) a, b, c or d and / or e can be automated partially to completely.
  • connection of the prosthetic tooth, the prosthetic teeth or the dental arch with the prosthetic base plate takes place in particular without any edge gap.
  • one or more flowable, dentin-colored compositions are preferably used as the polymerizable dental composition, which comprise monomers, in particular di(meth)acrylates, and optionally fillers, in particular dental glasses.
  • the composition preferably has a viscosity of 10 2 to 10 6 mPas. A viscosity of 2 * 10 2 mPas after a load lasting 248 seconds, of approximately 5 * 10 5 mPas during the build-up of the load and of approximately 10 6 mPas at rest is preferred.
  • the method according to the invention allows in a special way an optimal adjustment of the geometry and/or tooth colors and/or gingiva colors as well as their progression and gradation in selected areas of the prosthetic care in an automated method.
  • the respective dentin color can be optimally adapted to the tooth color of the generatively produced shell of the dental prosthesis or dental arch. Therefore, the method according to the invention allows complete prosthetic restorations to be manufactured very economically in an automated process while at the same time maintaining the highest aesthetic standards for the prosthetic restoration. In this way, the tooth colors can be economically adapted to the remaining teeth.
  • the dental, polymerizable compositions for the generative production of the prosthetic teeth, the light-curing dentin-colored composition and the composition for the generative production of the prosthesis base can include, for example, the following components.
  • a light-curing composition is preferably used to produce the aforementioned prosthesis parts.
  • a typical composition may comprise (a) at least one curable monomer and/or polymer component and optionally (b) at least one filler component.
  • the proportion of monomers in the overall composition can be up to 100% by weight, from 40 to 99.99% by weight is preferred, in particular 50 to 99.99% by weight or from 98% by weight to 99.99% by weight, which may contain 0.01 to 2% by weight of initiators, stabilizers or auxiliaries.
  • a composition as filler component (b) can have a total filler content in relation to the overall composition of 10 to 98% by weight, in particular 60 to 95% by weight, comprising (b.1) 10 to 35% by weight, in particular 10 to 30% by weight, preferably 10 to 25% by weight, particularly preferably 15 to 25% by weight, in particular silanized oxide particles and / or (b.2) at least one dental glass from 0 to 75% by weight, in particular from 10 to 65% by weight, particularly preferably from 40 to 60% by weight, such as 45 to 50 or 50 to 65% by weight, preferably a mixture of dental glasses of 50 to 90% coarse and 10 to 50% fine-particle dental glasses are used, which have a size ratio, based on the average particle size (d 50 value), from fine-particle to coarse-particle of 30:1 to 1:30, and optionally, (b.3) 0.5 to 10 % by weight of non-agglomerated nanofillers with particle sizes of 1 to 50 nm.
  • Non-agglomerated nanofillers are known per se and, for example, in WO0130305A1 or using the example of SiO 2 in DE19617931A1 described. They can preferably be selected from the group SiO 2 , ZrO 2 , TiO 2 , Al 2 O 3 and from mixtures of at least two of these substances. You can - as in DE19617931A1 described - be dispersed in organic solvents, but can also be added to water or solvent mixtures containing water.
  • Barium glass powder preferably barium glass-aluminum borosilicate glasses, and/or strontium glass powder are particularly suitable as dental glasses.
  • the average particle size of the coarse-particle dental glasses is preferably 5-10 [micro]m, in particular around 7 [micro]m, and that of the fine-particle 0.5 to 2 [micro]m, in particular 1 [micro]m.
  • Other optional dental glasses have, for example, average grain sizes of 2-5 or 10-50 [micro]m.
  • the filler component can therefore have dental glasses with a total of three or more grain fractions. It can also contain other conventional fillers common in the dental field, such as quartz, glass ceramic or mixtures thereof. In addition, the composites can contain fillers to achieve increased radiopacity.
  • the dental material preferably comprises the following monomers or polymers as a curable monomer and/or polymer component:
  • the monomers commonly used in the dental field can be considered as monomers: examples are free-radically polymerizable monomers such as mono(meth)acrylates, Methyl, ethyl, butyl, benzyl, furfuryl or phenyl (meth) acrylate, polyfunctional monomers such as polyfunctional acrylates or methacrylates, e.g. bisphenol A di(meth)acrylate, bis-GMA (an addition product from methacrylic acid and bisphenol A diglycidyl ether), UDMA (urethane dimethacrylate), e.g.
  • crosslinker monomer at least one monomer selected from the following or mixtures of these can be used: 2,2-bis-4-(3-methacryloxy-2-hydroxypropyl)-phenylpropane) (Bis-GMA), i.e. the reaction product of glycidyl methacrylate and bisphenol -A (containing OH groups), and 7,7,9-trimethyl-4,13-dioxo-3,14-dioxa-5,12-diazahexadecane-1,16-diyldimethacrylate (UDMA), i.e.
  • Bis-GMA 2,2-bis-4-(3-methacryloxy-2-hydroxypropyl)-phenylpropane)
  • UDMA 7,7,9-trimethyl-4,13-dioxo-3,14-dioxa-5,12-diazahexadecane-1,16-diyldimethacrylate
  • reaction products of glycidyl methacrylate with other bisphenols such as bisphenol-B (2,2'-bis-(4-hydroxyphenyl)-butane), bisphenol-F (4,4'-bis(hydroxyphenyl)-methane), ( 2,2'-methylenediphenol) or 4,4'-dihydroxydiphenyl, as well as reaction products of 2 moles of HEMA or 2-hydroxypropyl (meth)acrylate with, in particular 1 mole, known diisocyanates, such as hexamethylene diisocyanate, m-xylylene diisocyanate or tolylene diisocyanate, as crosslinking monomers suitable.
  • diisocyanates such as hexamethylene diisocyanate, m-xylylene diisocyanate or tolylene diisocyanate, as crosslinking monomers suitable.
  • suitable multifunctional crosslinkers include: diethylene glycol di(meth)acrylate, trimethylolpropane tri(meth)acrylate, pentaerythritol tetra(meth)acrylate and butanediol di(meth)acrylate, 1,10-decanediol di(meth)acrylate, 1, 12-Dodecanediol di(meth)acrylate.
  • the dental material can preferably be monomers and/or polymers, including those mentioned below, as a curable monomer and/or polymer component include: One or more ethylenically unsaturated compounds with or without acid functionality.
  • acrylates As well as mono-, di- or poly-(meth)acrylates, ie acrylates and methacrylates, such as methyl (meth)acrylate, ethyl acrylate, isopropyl methacrylate, n-hexyl acrylate, stearyl acrylate, allyl acrylate, glycerol triacrylate, ethylene glycol diacrylate, diethylene glycol diacrylate, triethylene glycol dimethacrylate, 1,3- Propanediol (meth)acrylate, trimethylolpropane triacrylate, 1,2,4-butanetriol trimethacrylate, 1,4-cyclohexanediol diacrylate, pentaerythritol tetra(meth)acrylate, sorbitol hexacrylates, tetrahydrofurfuryl (meth)acrylate, bis[1-(2-acryloxy)] -p-ethoxyphenyldimethyl
  • the polymerizable component may also have hydroxyl groups and ethylenically unsaturated groups in a single molecule.
  • examples of such materials include hydroxyalkyl (meth)acrylates such as 2-hydroxyethyl (meth)acrylate and 2-hydroxypropyl (meth)acrylate; glycerol mono- or di-(meth)acrylate; Trimethylolpropane mono- or di-(meth)acrylate; Pentaerythritol mono-, di- and tri-(meth)acrylate; Sorbitol mono-, di-, tri-, terra- or penta-(meth)acrylate and 2,2-bis[4-(2-hydroxy-3-methacryloxypropoxy)phenyl]propane (BisGMA) or mixtures of ethylenically unsaturated compounds.
  • hydroxyalkyl (meth)acrylates such as 2-hydroxyethyl (meth)acrylate and 2-hydroxypropyl (meth)acrylate
  • the curable or polymerizable component may be PEGDMA (polyethylene glycol dimethacrylate with a molecular weight of about 400 g/mol), GDMA (glycerine dimethacrylate), TEGDMA (triethylene glycol dimethacrylate) and/or NPGDMA (neopentyl glycol dimethacrylate) and mixtures thereof.
  • PEGDMA polyethylene glycol dimethacrylate with a molecular weight of about 400 g/mol
  • GDMA glycol dimethacrylate
  • TEGDMA triethylene glycol dimethacrylate
  • NPGDMA neopentyl glycol dimethacrylate
  • the composites contain a polymerization initiator, for example an initiator for radical polymerization.
  • a polymerization initiator for example an initiator for radical polymerization.
  • the mixtures can be cold-crosslinked, cross-linked by radiation, i.e. UV- or VIS-crosslinked, or polymerizable by applying heat.
  • Known peroxides can be used as initiators for temperature-induced polymerization, such as dibenzoyl peroxide, dilauroyl peroxide, tert-butyl peroctoate or tert-butyl perbenzoate, but also alpha, alpha'-azo-bis(isobutyroethyl ester), benzopinacol and 2,2'-dimethylbenzpinacol .
  • the initiators for temperature-induced polymerization can be used to harden the dentin-colored composition and/or to bond the prosthetic teeth to the prosthetic base plate.
  • Photoinitiators include, for example, benzoin alkyl ethers or esters, benzil monoketals, acylphosphine oxides or aliphatic and aromatic 1,2-diketo compounds, such as 2,2-diethoxyacetophenone, 9,10-phenanthrenequinone, diacetyl, furil, anisile, 4,4'-dichlorobenzil and 4,4' -Dialkoxybenzil or camphorquinone in question.
  • the photoinitiators are preferably used together with a reducing agent.
  • reducing agents are amines such as aliphatic or aromatic tertiary amines, for example N,N-dimethyl-p-toluidine or triethanolamine, cyanoethylmethylaniline, triethylamine, N,N-dimethylaniline, N-methyldiphenylamine, N,N-dimethyl-sym.-xylidine, N,N-3,5-tetramethylaniline and 4-dimethylaminobenzoic acid ethyl ester or organic phosphites.
  • amines such as aliphatic or aromatic tertiary amines, for example N,N-dimethyl-p-toluidine or triethanolamine, cyanoethylmethylaniline, triethylamine, N,N-dimethylaniline, N-methyldiphenylamine, N,N-dimethyl-sym.-xylidine, N,N-3,5-tetramethylaniline and 4-d
  • Common photoinitiator systems include camphorquinone plus ethyl 4-(N,N-dimethylamino)benzoate, 2-(ethylhexyl)-4-(N,N-dimethylamino)benzoate or N,N-dimethylaminoethyl methacrylate.
  • 2,4,6-Trimethylbenzoyldiphenylphosphine oxide is particularly suitable as an initiator for the polymerization initiated by UV light.
  • UV photoinitiators can be used alone, in Combination with a visible light initiator, a cold curing initiator and / or a temperature induced curing initiator can be used.
  • Radical-forming systems e.g. B. benzoyl or lauroyl peroxide is used together with amines such as N,N-dimethyl-sym.-xylidine or N,N-dimethyl-p-toluidine.
  • Dual curing systems can also be used, e.g. B. photoinitiators with amines and peroxides.
  • the initiators are preferably used in amounts of 0.01 to 1% by weight based on the total mass of the mixture.
  • the initiators for cold polymerization can be used to harden the dentin-colored composition or to bond the prosthetic teeth to the prosthetic base plate During cold polymerization, it can be useful if the composite material is divided into two components that are intended for curing by mixing. It is also possible to provide the material in such a way that it can be cured by VIS and/or UV light as well as by mixing two components.
  • the two components of the dentin-colored material can be present in two pastes or as a powder/liquid system.
  • the radical initiator system required for the polymerization is, depending on the reaction conditions or polymerization system, divided into the two pastes or contained in the liquid component (A) and/or the powdery component (B).
  • the initiator system in base mixtures for cold polymers, the initiator system is usually present in both components, the liquid component and the powdery component, and is therefore combined when these components are mixed.
  • the initiator In the base materials for hot polymers, the initiator is usually present in the polymer component, ie the powdery component. Only during mixing does the initiator get into the liquid monomer component.
  • prosthesis starting materials can be provided in which the initiator component (C) is present in the powdery component (B), in particular in the form of peroxides, perketals, peresters and/or azo compounds. This can be e.g. B. also about residual contents in the production of the powdery components non-reacted initiator components, e.g. B. peroxides such as dibenzoyl peroxide.
  • suitable initiators for the polymerization reaction of cold or autopolymerizing starting mixtures are those with which radical polymerization reactions can be started.
  • Preferred initiators are peroxides such as dibenzoyl peroxide, dilauroyl peroxide and di-t-butyl peroxide as well as azo compounds such as azobis(isobutyronitrile) (AIBN).
  • LPO dilauroyl peroxide
  • BPO dibenzoyl peroxide
  • t-BPEH tert-butyl per-2-ethylhexanoate
  • AIBN 2,2'-azobis-(isobutyronitrile)
  • DTBP di-tert-butyl peroxide.
  • suitable activators e.g. B. aromatic amines
  • suitable amines include N,N-dimethyl-p-toluidine, N,N-dihydroxyethyl-p-toluidine and diethyl p-dibenzyl aminobenzoate.
  • the amines regularly function as co-initiators and are usually present in an amount of up to 0.5% by weight based on the overall composition.
  • Redox systems are also suitable as radical initiator systems, in particular combinations of dibenzoyl peroxide, dilauroyl or camphorquinone with amines such as N,N-dimethyl-p-toluidine, NN-dihydroxyethyl-p-toluidine and diethyl p-dimethylaminobenzoate.
  • redox systems which can also be used are those which, in addition to a peroxide, also contain ascorbic acid or its derivatives, barbituric acid or a barbituric acid derivative or a sulfinic acid as a reducing agent.
  • such a redox system contains barbituric acid or thiobarbituric acid or a barbituric acid or thiobarbituric acid derivative (for example 0.01 - 10% by weight), at least one copper salt or a copper complex (for example 0.1 to 8% by weight) and at least a compound with an ionic halogen atom (for example 0.05 to 7% by weight), in each case with respect to the content of the initiator system of 0.01 to 1% by weight the overall composition.
  • suitable components of the above-mentioned redox system include 1-benzyl-5-phenylbarbituric acid, copper acetylacetonate and benzyl-dibutylammonium chloride.
  • compositions are preferably cured by redox-induced radical polymerization at room temperature or at a slightly elevated temperature under slight pressure in order to avoid the formation of bubbles.
  • Barbituric acids in conjunction with copper and chloride ions are used as initiators for the polymerization carried out at room temperature. This system is characterized by high color stability.
  • the liquid composition for the generative production of the at least one prosthetic tooth preferably comprises at least one monomer, in particular at least one di(meth)acrylate, particularly preferably the composition comprises UDMA, ethoxylated bisphenol-A and optionally dental glasses and fumed silica.
  • the generatively produced prosthetic tooth (6) preferably has a translucency of > 50%.
  • the polymerized dentin-colored dental composition has a translucency of greater than or equal to 35% and/or the at least one generatively produced prosthetic tooth or the dental arch has a translucency of greater than or equal to 55 to 65%.
  • the liquid composition for the generative production of the prosthesis base (plate) preferably comprises at least one monomer, in particular at least one di(meth)acrylate and optionally fillers such as dental glasses with d 50 ⁇ 2 ⁇ m and optionally fumed silicas.
  • the subject of the invention is also one Complete denture.
  • the invention also relates to the use of a flowable, dentin-colored, polymerizable dental composition comprising dental glasses in the method according to the invention.
  • the subject of the invention is the use of a complete denture obtainable by the method according to the invention as (i) a real model of a provisional prosthesis for adapting the provisional prosthesis to the patient's dental situation or (ii) as a real model of a provisional prosthesis for adapting the provisional prosthesis to the Dental situation of the patient and for scanning the provisional prosthesis adapted in this way and optionally for adapting the virtual model of the at least one prosthetic tooth or prosthetic teeth, in particular a dental arch, and the prosthetic base plate for the generative production of the patient's complete prosthesis.
  • Figure 1 shows a sectioned total prosthesis 0 from the digital data of the virtual model of the surface 0 of the prosthetic molded part. This data set is then split using the software (file splitting) into the digital data of the prosthesis base (plate), which is in Figure 2a are shown as a prosthesis base plate 2 and in the digital data of the dental prostheses 1 , which are in Figure 2b are shown as the surface shell of the dental prostheses. At the neck of the tooth (underside not visible) is the cervical area of the prosthetic tooth as 1.2 . Furthermore, in Figure 1 the supragingival surface 2.3 of the denture base (above the gums) is shown.
  • the crestal area 2.2 is also shown into which the virtual model of the at least one prosthetic tooth 1 or the prosthetic teeth 1 and the virtual model of the prosthetic base 2 were divided or alternatively the closed crestal surface 2.2 in this area.
  • the cervical area 1.2 of the prosthetic tooth is joined, in particular by polymerizing excess dental composition 12 after the dental prosthesis and the prosthetic base plate have been pressed together.
  • Figure 3 shows a sectional view of the real total prosthesis 5 produced with prosthetic tooth 6.
  • the prosthetic tooth has a defined wall thickness 7 and a polymerized composition 8 in the lumen 4.
  • the prosthetic tooth 6 was joined to a prosthetic base plate 9 .
  • Figure 4a shows a cross section through the virtual model 1 of the tooth of the full body model 11 with a constructed defined wall thickness 3 and remaining lumen or cavity 4.
  • 1.2 represents the cervical area of the tooth.
  • This full body model is turned into a stereolithography process the real prosthetic tooth 6 with defined wall thickness 7 and lumen 4 is produced, as in Figure 4b shown.
  • the Figure 4c represents a further process step in which the dental, dentin-colored composition 12 is filled into the lumen 4 of the prosthetic tooth 6 .
  • the composition 12 can be polymerized and further dental composition 12 can then be filled into the lumen.
  • the prosthetic tooth 6 is placed on the prosthetic base 9 , pressed together and polymerized with UV light.
  • the complete prosthesis 5 produced in this way can be refinished in the light oven.

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  • Health & Medical Sciences (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Dentistry (AREA)
  • Epidemiology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Engineering & Computer Science (AREA)
  • Manufacturing & Machinery (AREA)
  • Dental Prosthetics (AREA)
EP20163304.7A 2015-03-24 2016-03-22 Verfahren zur herstellung einer teil- oder totalprothese sowie prothese erhältlich nach diesem verfahren Active EP3689290B1 (de)

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DE102015104394.7A DE102015104394B4 (de) 2015-03-24 2015-03-24 Verfahren zur Herstellung einer Teil- oder Totalprothese sowie Prothese erhältlich nach diesem Verfahren
EP16711816.5A EP3280348B1 (de) 2015-03-24 2016-03-22 Verfahren zur herstellung einer teil- oder totalprothese sowie prothese erhältlich nach diesem verfahren
PCT/EP2016/056252 WO2016150955A1 (de) 2015-03-24 2016-03-22 Verfahren zur herstellung einer teil- oder totalprothese sowie prothese erhältlich nach diesem verfahren

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EP3689290A3 (de) 2020-10-21
US20180078348A1 (en) 2018-03-22
JP2018509248A (ja) 2018-04-05
DE102015104394A9 (de) 2017-08-24
CN107427347A (zh) 2017-12-01
DE102015104394A1 (de) 2016-09-29
EP3689290A2 (de) 2020-08-05
WO2016150955A1 (de) 2016-09-29
EP3689290C0 (de) 2023-11-22
JP6861640B2 (ja) 2021-04-21
EP3280348A1 (de) 2018-02-14
EP3280348B1 (de) 2020-06-03
CN107427347B (zh) 2021-02-05

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